|Numéro de publication||US7938836 B2|
|Type de publication||Octroi|
|Numéro de demande||US 11/259,614|
|Date de publication||10 mai 2011|
|Date de dépôt||25 oct. 2005|
|Date de priorité||23 oct. 2003|
|État de paiement des frais||Payé|
|Autre référence de publication||CA2627030A1, CA2627167A1, EP1945114A2, EP1945115A2, US8038680, US20060155297, US20070167951, WO2007050629A2, WO2007050629A3, WO2007050640A2, WO2007050640A3|
|Numéro de publication||11259614, 259614, US 7938836 B2, US 7938836B2, US-B2-7938836, US7938836 B2, US7938836B2|
|Inventeurs||Stephen D. Ainsworth, Robert L. Assell, Bradley J. Wessman|
|Cessionnaire d'origine||Trans1, Inc.|
|Exporter la citation||BiBTeX, EndNote, RefMan|
|Citations de brevets (121), Référencé par (15), Classifications (46), Événements juridiques (7)|
|Liens externes: USPTO, Cession USPTO, Espacenet|
This application claims priority and incorporates by reference a and commonly assigned U.S. Provisional Application No. 60/621,730 filed Oct. 25, 2004 for Multi-Part Assembly for Introducing Axial Implants into the Spine. This application claims priority and incorporates by reference both U.S. patent application Ser. No. 11/256,810 filed Oct. 24, 2005 for Spinal Motion Preservation Assemblies and a U.S. Provisional Application No. 60/621,148 filed Oct. 22, 2004 for Spinal Mobility Preservation Assemblies. This application claims priority and incorporates by reference four and commonly assigned U.S. patent application Ser. Nos. 10/972,184, 10/927,039, 10/972,040, and 10/972,176 all filed on Oct. 22, 2004. These four applications claim priority to two provisional application 60/558,069 filed Mar. 31, 2004 and 60/513,899 filed Oct. 23, 2003. Priority to these two provisionals is claimed through the four applications and the provisionals are incorporated by reference. This application also claims priority to and commonly assigned U.S. patent application Ser. No. 11/199,541 filed Aug. 8, 2005 and Provisional Application 60/599,989 filed Aug. 9, 2004 which is claimed as a priority document for the '541 application. Both of these applications are incorporated by reference.
This application extends the work done by TranS1 Inc. and incorporates by reference a set of United States applications, provisional applications, and issued patents including: 60/182,748 filed Feb. 16, 2000; Ser. No. 09/640,222 filed Aug. 16, 2000 (now issued as U.S. Pat. No. 6,575,979); Ser. No. 10/459,149 filed Jun. 11, 2003; Ser. No. 09/684,820 filed Oct. 10, 2000 (now issued as U.S. Pat. No. 6,558,386); Ser. No. 10/430,751 filed May 6, 2003; 60/182,748 filed Feb. 16, 2000; Ser. No. 09/782,583 filed Feb. 13, 2001 (issued as U.S. Pat. No. 6,558,390); Ser. No. 09/848,556 filed May 3, 2001; Ser. No. 10/125,771 filed Apr. 18, 2002 (issued as U.S. Pat. No. 6,899,716); Ser. No. 10/990,705 filed Nov. 17, 2004; Ser. No. 10/430,841 filed May 6, 2003; Ser. No. 09/710,369 filed Nov. 10, 2000 (issued as U.S. Pat. No. 6,740,090); Ser. No. 10/853,476 filed May 25, 2004; Ser. No. 09/709,105 filed Nov. 10, 2000 (issued as U.S. Pat. No. 6,790,210); Ser. No. 09/782,534 filed Feb. 13, 2001; application Ser. Nos. 10/971,779, 10/971,781, 10/971,731, 10/972,077, 10/971,765, 10/972,065, 10/971,775, 10/971,299, 10/971,780, all filed Oct. 22, 2004; 60/706,704 filed Aug. 9, 2005; Ser. No. 11/189,943 filed Jul. 26, 2005, Ser. No. 10/309,416 now U.S. Pat. No. 6,921,403 filed Dec. 3, 2002. While these applications have been incorporated by reference to provide additional detail it should be noted that these other applications (including those that have subsequently issued as patents) were written at an earlier time and had a different focus from the present application. Thus, to the extent that the teachings or use of terminology differs in any of these incorporated applications from the present application, the present application controls.
The present invention relates generally to implantable device assemblies, instrumentation systems, and methods for accessing and a spinal motion segment via a minimally-invasive trans-sacral approach (as described in U.S. Pat. No. 6,558,390 which is incorporated herein by reference) and procedures comprising the deployment of implantable components and assemblies that are anchored in bone that can be used to position, manage motion, and stabilize a vertebral motion segments in the human spine to relieve lower back pain, restore physiological function of the lumbar spine, and prevent progression or transition of degenerative disease. More specifically, the present invention generally relates to spinal motion preservation assemblies (MPA) generally introduced percutaneously through tissue to an access point on the spine in a minimally invasive, low trauma manner, to provide therapy to the spine.
The present invention is an extension of work assigned to TranS1 Inc. with a principle place of business located in Wilmington, N.C. Much of the work is described in great detail in the many applications referenced above and incorporated by reference into this application. Accordingly, the background of the invention provided here does not repeat all of the detail provided in the earlier applications, but instead highlights how the present invention adds to this body of work.
The spinal column is a complex system of bone segments (vertebral bodies and other bone segments) which are in most cases separated from one another by discs in the intervertebral spaces (sacral vertebrae are an exception).
The vertebrae of the spinal cord are conventionally subdivided into several sections. Moving from the head to the tailbone, the sections are cervical 104, thoracic 108, lumbar 112, sacral 116, and coccygeal 120. The individual vertebral bodies within the sections are identified by number starting at the vertebral body closest to the head. Of particular interest in this application are the vertebral bodies in the lumbar section and the sacral section. As the various vertebral bodies in the sacral section are usually fused together in adults, it is sufficient and perhaps more descriptive to merely refer to the sacrum rather than the individual sacral components.
It is useful to set forth some of the standard medical vocabulary before getting into a more detailed discussion of the background of the present invention. In the context of the this discussion: anterior refers to in front of the spinal column; (ventral) and posterior refers to behind the column (dorsal); cephalad means towards the patient's head (sometimes “superior”); caudal (sometimes “inferior”) refers to the direction or location that is closer to the feet. As the present application contemplates accessing the various vertebral bodies and intervertebral spaces through a preferred approach that comes in from the sacrum and moves towards the head, proximal and distal are defined in context of this channel of approach. Consequently, proximal is closer to the beginning of the channel and thus towards the feet or the surgeon, distal is further from the beginning of the channel and thus towards the head, or more distant from the surgeon.
The individual motion segments within the spinal columns allow movement within constrained limits and provide protection for the spinal cord. The discs are important to bear and distribute the large forces that pass through the spinal column as a person walks, bends, lifts, or otherwise moves. Unfortunately, for a number of reasons referenced below, for some people, one or more discs in the spinal column will not operate as intended. The reasons for disc problems range from a congenital defect, disease, injury, or degeneration attributable to aging. Often when the discs are not operating properly, the gap between adjacent vertebral bodies is reduced and this causes additional problems including pain.
There are currently over 700,000 surgical procedures performed annually to treat lower back pain in the U.S. In 2004, it is conservatively estimated that there will be more than 200,000 lumbar fusions performed in the U.S., and more than 300,000 worldwide, representing approximately a $1B endeavor in an attempt to alleviate patients' pain. Approximately 60% of spinal surgery takes place in the lumbar spine, and of that portion approximately 80% involves the lower lumbar vertebrae designated as the fourth lumbar vertebra (“L4”), the fifth lumbar vertebra (“L5”), and the first sacral vertebra (“S1”). Persistent low back pain is often attributable to degeneration of the disc between L5 and S1. (See edge between the lumbar region 112 and the sacrum 116 in
A range of therapies have been developed to alleviate the pain associated with disc problems. One class of solutions is to remove the failed disc and then fuse the two adjacent vertebral bodies together with a permanent but inflexible spacing, also referred to as static stabilization. As mentioned above, an estimated 300,000 fusion operations take place each year. Fusing one section together ends the ability to flex in that motion segment. While the loss of the normal physiologic disc function for a motion segment through fusion of a motion segment may be better than continuing to suffer from the pain, it would be better to alleviate the pain and yet retain all or much of the normal performance of a healthy motion segment.
Another class of therapies attempts to repair the disc so that it resumes operation with the intended intervertebral spacing and mechanical properties. One type of repair is the replacement of the original damaged disc with a prosthetic disc. This type of therapy is called by different names such as dynamic stabilization or spinal motion preservation.
The Operation of the Spine
The bodies of successive lumbar, thoracic and cervical vertebrae articulate with one another and are separated by the intervertebral spinal discs. Each spinal disc comprises a fibrous cartilage shell enclosing a central mass, the “nucleus pulposus” (or “nucleus” herein) that provides for cushioning and dampening of compressive forces to the spinal column. The shell enclosing the nucleus comprises cartilaginous endplates adhered to the opposed cortical bone endplates of the cephalad and caudal vertebral bodies and the “annulus fibrosus” (or “annulus” herein) comprising multiple layers of opposing collagen fibers running circumferentially around the nucleus pulposus and connecting the cartilaginous endplates. The natural, physiological nucleus is comprised of hydrophilic (water attracting) mucopolysacharides and fibrous strands (protein polymers). The nucleus is relatively inelastic, but the annulus can bulge outward slightly to accommodate loads axially applied to the spinal motion segment.
The intervertebral discs are anterior to the spinal canal and located between the opposed end faces or endplates of a cephalad and a caudal vertebral bodies. The inferior articular processes articulate with the superior articular processes of the next succeeding vertebra in the caudal (i.e., toward the feet or inferior) direction. Several ligaments (supraspinous, interspinous, anterior and posterior longitudinal, and the ligamenta flava) hold the vertebrae in position yet permit a limited degree of movement. The assembly of two vertebral bodies, the interposed, intervertebral, spinal disc and the attached ligaments, muscles and facet joints is referred to as a “spinal motion segment”.
The relatively large vertebral bodies located in the anterior portion of the spine and the intervertebral discs provide the majority of the weight bearing support of the vertebral column. Each vertebral body has relatively strong, cortical bone layer comprising the exposed outside surface of the body, including the endplates, and weaker, cancellous bone comprising the center of the vertebral body.
The nucleus pulposus that forms the center portion of the intervertebral disc consists of 80% water that is absorbed by the proteoglycans in a healthy adult spine. With aging, the nucleus becomes less fluid and more viscous and sometimes even dehydrates and contracts (sometimes referred to as “isolated disc resorption”) causing severe pain in many instances. The spinal discs serve as “dampeners” between each vertebral body that minimize the impact of movement on the spinal column, and disc degeneration, marked by a decrease in water content within the nucleus, renders discs ineffective in transferring loads to the annulus layers. In addition, the annulus tends to thicken, desiccate, and become more rigid, lessening its ability to elastically deform under load and making it susceptible to fracturing or fissuring, and one form of degeneration of the disc thus occurs when the annulus fissures or is torn. The fissure may or may not be accompanied by extrusion of nucleus material into and beyond the annulus. The fissure itself may be the sole morphological change, above and beyond generalized degenerative changes in the connective tissue of the disc, and disc fissures can nevertheless be painful and debilitating. Biochemicals contained within the nucleus are enabled to escape through the fissure and irritate nearby structures.
A fissure also may be associated with a herniation or rupture of the annulus causing the nucleus to bulge outward or extrude out through the fissure and impinge upon the spinal column or nerves (a “ruptured” or “slipped” disc). With a contained disc herniation, the nucleus may work its way partly through the annulus but is still contained within the annulus or beneath the posterior longitudinal ligament, and there are no free nucleus fragments in the spinal canal. Nevertheless, even a contained disc herniation is problematic because the outward protrusion can press on the spinal cord or on spinal nerves causing sciatica.
Another disc problem occurs when the disc bulges outward circumferentially in all directions and not just in one location. This occurs when, over time, the disc weakens bulges outward and takes on a “roll” shape. Mechanical stiffness of the joint is reduced and the spinal motion segment may become unstable, shortening the spinal cord segment. As the disc “roll” extends beyond the normal circumference, the disc height may be compromised, and foramina with nerve roots are compressed causing pain. Current treatment methods other than spinal fusion for symptomatic disc rolls and herniated discs include “laminectomy” which involves the surgical exposure of the annulus and surgical excision of the symptomatic portion of the herniated disc followed by a relatively lengthy recuperation period. In addition, osteophytes may form on the outer surface of the disc roll and further encroach on the spinal canal and foramina through which nerves pass. The cephalad vertebra may eventually settle on top of the caudal vertebra. This condition is called “lumbar spondylosis”.
Various other surgical treatments that attempt to preserve the intervertebral spinal disc and to simply relieve pain include a “discectomy” or “disc decompression” to remove some or most of the interior nucleus thereby decompressing and decreasing outward pressure on the annulus. In less invasive microsurgical procedures known as “microlumbar discectomy” and “automated percutaneous lumbar discectomy”, the nucleus is removed by suction through a needle laterally extended through the annulus. Although these procedures are less invasive than open surgery, they nevertheless suffer the possibility of injury to the nerve root and dural sac, perineural scar formation, re-herniation of the site of the surgery, and instability due to excess bone removal. In addition, they generally involve the perforation of the annulus.
Although damaged discs and vertebral bodies can be identified with sophisticated diagnostic imaging, existing surgical interventions and clinical outcomes are not consistently satisfactory. Furthermore, patients undergoing such fusion surgery experience significant complications and uncomfortable, prolonged convalescence. Surgical complications include disc space infection; nerve root injury; hematoma formation; instability of adjacent vertebrae, and disruption of muscle, tendons, and ligaments, for example.
Several companies are pursuing the development of prosthesis for the human spine, intended to completely replace a physiological disc, i.e., an artificial disc. In individuals where the degree of degeneration has not progressed to destruction of the annulus, rather than a total artificial disc replacement, a preferred treatment option may be to replace or augment the nucleus pulposus, involving the deployment of a prosthetic disc nucleus. As noted previously, the normal nucleus is contained within the space bounded by the bony vertebrae above and below it and the annulus fibrosus, which circumferentially surrounds it. In this way the nucleus is completely encapsulated and sealed with the only communication to the body being a fluid exchange that takes place through the bone interface with the vertebrae, known as the endplates.
The hydroscopic material comprising the physiological nucleus has an affinity for water (and swells in volume) which is sufficiently powerful to distract (i.e., elevate or “inflate”) the intervertebral disc space, despite the significant physiological loads that are carried across the disc in normal activities. These forces, which range from about 0.4× to about 1.8× body weight, generate local pressure well above normal blood pressure, and the nucleus and inner annulus tissue are, in fact, effectively avascular.
The existence of the nucleus as a cushion (e.g., the nucleus is the “air” in the “tire” known as a spinal disc), and the annulus, as a flexible member, contributes to the range of motion in the normal disc. Range of motion is described in terms of degrees of freedom (i.e., translation and rotation about three orthogonal planes relative to a reference point, the instantaneous center of rotation around the vertical axis of the spine).
Pure distraction rarely occurs and is usually a combination of tension and compression on the spinal joints depending on the direction of applied force. An example of a distraction force is therapeutic spinal traction to “unload” the spine.
In the context of the present invention, as used herein the term distraction refers procedurally to an elevation in height that increases the intervertebral disc space resulting from introduction of the motion preservation assembly or prosthetic nucleus device (“PND”), which may be achieved either in the axial deployment of the device itself, or assisted by means of a temporary distraction rod, during implantation. Temporary distraction refers to elevation of disc height by means, such as a distraction rod, which is subsequently removed but wherein the elevation is retained intra-operatively, while the patient remains prone. Thus, the device may be inserted into an elevated disc space first created by other distraction means, and thereafter physical presence and dimensionality of the inserted device is key to preserving that height space, to decompress the disc and alleviate pain caused by nerve impingement.
To date, drawbacks of currently contemplated or deployed prosthetic nucleus devices include subsidence; their tendency to extrude or migrate; to erode the bone; to degrade with time, or to fail to provide sufficient biomechanical load distribution and support. Some of these drawbacks relate to the fact that their deployment typically involves a virtually complete discectomy of the disc achieved by instruments introduced laterally through the patient's body to the disc site and manipulated to cut away or drill lateral holes through the disc and adjoining cortical bone. The endplates of the vertebral bodies, which comprise very hard cortical bone and help to give the vertebral bodies needed strength, are usually weakened or destroyed during the drilling. The vertebral endplates are special cartilage structures that surround the top and bottom of each vertebra and are in direct contact with the disc. They are important to the nutrition of the disc because they allow the passage of nutrients and water into the disc. If these structures are injured, it can lead to deterioration of the disc and altered disc function. Not only do the large laterally drilled hole or holes compromise the integrity of the vertebral bodies, but the spinal cord can be injured if they are drilled too posterior.
Alternatively, current devices are sometimes deployed through a surgically created or enlarged hole in the annulus. The annulus fibrosus consists of tough, thick collagen fibers. The collagen fibers which comprise the annulus fibrosus are arranged in concentric, alternating layers. Intra-layer orientation of these fibers is parallel, however, each alternating (i.e., interlayer) layers' collagen fibers are oriented obliquely (˜120). This oblique orientation allows the annulus to resist forces in both vertical and horizontal directions. Axial compression of a disc results in increased pressure in the disc space. This pressure is transferred to the annulus in the form of loads (stresses) perpendicular to the wall of the annulus. With applied stress, these fibrous layers are put in tension and the angle from horizontal decreases to better resist the load, i.e., the annulus works to resist these perpendicular stresses by transferring the loads around the circumference of the annulus (Hoop Stress). Vertical tension resists bending and distraction (flexion and extension). Horizontal tension resists rotation and sliding (i.e., twisting). While the vertical components of the annulus' layers enable the disc to withstand forward and backward bending well, only half of the horizontal fibers of the annulus are engaged during a rotational movement. In general, the disc is more susceptible to injury during a twisting motion, deriving its primary protection during rotation from the posterior facet joints; however, this risk is even greater if and when the annulus is compromised.
Moreover, annulus disruption will remain post-operatively, and present a pathway for device extrusion and migration in addition to compromising the physiological biomechanics of the disc structure. Other devices, in an attempt to provide sufficient mechanical integrity to withstand the stresses to which they will be subjected, are configured to be so firm, stiff, and inflexible that they tend to erode the bone or become imbedded, over time, in the vertebral bodies, a phenomenon known as “subsidence”, sometimes also termed “telescoping”. The result of subsidence is that the effective length of the vertebral column is shortened, which can subsequently cause damage to the nerve root and nerves that pass between the two adjacent vertebrae.
Tools used in the deployment of spinal implant assemblies such as spinal mobility preservation assemblies are disclosed. These tools assist in the three steps which are commonly part of the deployment process although some deployments may not require all three steps and some methods of deployment perform two of the steps at the same time.
Generally, the assemblies may be inserted axially within the spine, following either partial or complete nucleectomy and through a cannula that is docked against the sacrum, into a surgically de-nucleated disc space, from said access point across a treatment zone. In one aspect of the invention, prosthetic or augmentation materials are introduced, through at least one vertebral body or into at least one disc space. The introduction of the spinal motion preservation assemblies is accomplished without the need to surgically create or deleteriously enlarge an existing hole in the annulus fibrosus of the disc, and their deployment therapeutically preserves the physiological function of natural disc structures.
In one aspect of the invention, risks associated with implant expulsion, migration, or subsidence (that are inherently less for the motion preservation assemblies of the present invention) may be even further mitigated by retention means, e.g., by external, self-tapping threads configured to distribute stress evenly over a large surface area, that engage the vertebral body and secure (i.e., anchor) the implant assemblies therein.
The screw threads are typical of “cancellous” type bone threads known in the art. The threads are typically cut with generally flat faces on the flights of the thread with the most flat of the faces oriented in the direction of the applied load. In one embodiment, the thread profile generally comprises deep flights with an asymmetric thread form, which provides the advantage of improved weight bearing and load distribution. Threads are formed on root portions and extend as continuous threads from the trailing end to the leading end of the respective threaded sections. The screw threads include multiple revolutions that are spaced apart along the roots by inter-thread spacings. The proximal component and distal component threads are like-handed (i.e. the threads turn in the same direction) so that both screw threads are right-handed or so that both are left-handed.
The self-tapping threads may or may not be configured to assist in distraction of adjacent vertebral bodies within a motion segment, i.e., may or may not be configured with distal and proximal components (anchored in superior and inferior vertebral bodies, respectively) with differential thread pitches, and wherein the distal anchor has a major diameter that is less than that of the proximal anchor. Clockwise rotation of embodiments configured with right-handed threads (i.e., differential pitch and major diameters as just described) advances assemblies axially and distracts the superior and inferior vertebral bodies within a motion segment relative one to the other.
In the context of this application, “dynamic” refers to non-static devices with an inherent ability to allow mobility by enabling or facilitating forces or load bearing that assist or substitute for physiological structures that are otherwise compromised, weakened or absent. The mobility preservation assemblies (MPA) introduced by an axial trans-sacral approach provide dynamic stabilization (DS) across a progression-of-treatment interventions for treating symptomatic discogenic pain, ranging from treatment in patients where little degeneration or collapse is evident radio-graphically, to those for whom prosthetic nucleus devices or total disc replacements are indicated. For example, a prosthetic nucleus (PN) would be indicated in patients with a greater degree of degeneration and loss of disc height but not to the stage where advanced annular break-down is present. A prosthetic nucleus would go beyond dynamic stabilization by including an aggressive nucleectomy and subsequent filling of the de-nucleated space with an appropriate material. Here, the goal is to restore disc height and motion. Total disc replacement (TDR) is generally indicated with more advanced disease than with a prosthetic nucleus but where some annular function remains. The motion preservation assemblies can serve as prosthetic disc replacements (PDR) that are much less invasive (in terms of deployment) than traditional total disc replacements, and are configured so as to augment, preserve, restore, and/or manage the physiological function according to the intervention indicated. In general, the axial motion preservation assemblies are preferably configured as devices with an aspect ratio of greater than 1, i.e., the device dimension in the axial vertebral plane is greater than the device dimension in any orthogonal direction to that axial plane in close proximity to the physiological instantaneous center of axial rotation, and are deployed in an orientation in approximately the line of principal compressive stress, and placed at approximately the center of rotation vis á vis a human disc motion segment.
The present invention will now be described more fully hereinafter with reference to accompanying drawings in order to disclose selected illustrative embodiments. This invention may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein; rather these embodiments are provided so that the disclosure can be thorough and complete, and as part of the effort to convey the scope of the invention to those skilled in the art. Like numbers refer to like elements throughout.
Axial Trans-Sacral Access
The present invention contemplates the use of the axial trans-sacral access to the lumbo-sacral spine. The axial trans-sacral access method illustrated in
The discussion of
A brief overview of this method of accessing the spinal region to receive therapy is useful to provide context for the present invention. As shown in
In order to provide context to the present invention it is useful to briefly describe the major components of a an implanted spinal implant assembly of the type described in greater detail in pending U.S. patent application No. 11/256,810 filed Oct. 24, 2005 for Spinal Motion Preservation Assemblies. The specifics provided in
The major components of the motion preservation assembly 300 include the distal component (anchored in the superior, or distal vertebral body, herein also sometimes referred to as distal bone anchor) 340, proximal component (anchored in the inferior, or proximal vertebral body, herein also sometimes referred to as proximal bone anchor) 344, prosthetic nucleus 348 (generally including outer membrane 460), and a pivot 352. The outer membrane can be comprised of an elastomeric material, e.g. silicone rubber, such as that obtained from Nusil Silicone Technology located in Carpeneria, Calif., exhibiting elongation of between about 500% and about 1500% and most preferably about 1000% and having a wall thickness of 0.220 inches.
The distal bone anchor 340 shown in
The distal bone anchor 340 has a cavity 364 running from the distal face 366 of the distal bone anchor 340 to the proximal face 370 of the distal bone anchor 340. In this context, a face is the three dimensional surface of the part as viewed from that side, akin to the six three dimensional faces of die from a pair of dice. The cavity 364 is not of uniform cross section and serves several purposes. The distal end of the cavity 364 illustrates that the cavity can be used to allow the distal bone anchor 340 to be deployed over a guide wire. The cavity 364 includes an internal threaded section 368 which can be engaged by a driver, retention or extraction tool as described below. The cavity 364 in the distal bone anchor 340 shown in
The distal pivot cup 372 in turn has a cavity 380 which serves as a bearing surface for the distal end 384 of the pivot 352.
The pivot 352 shown in
The proximal bone anchor 344 has a set of external threads 404 including a lead-in section 408. The proximal bone anchor 344 has a cavity 412 that runs from the distal face 410 of the proximal bone anchor 344 to the proximal face 414 of the proximal bone anchor 344. The cavity 412 is not uniform in cross section. A portion of the cavity 412 has a set of internal threads 416. Preferably, the pitch of the set of internal thread 416 will be relatively fine (perhaps 16 threads per inch up to 64 threads per inch). In the particular motion preservation assembly shown in
Note that the distraction that can be achieved by rotation of the proximal pivot cup 420 is preferably used as an adjustment to alter the distribution of loading between the pivot and the prosthetic nucleus component of the motion preservation assembly. The primary means for achieving distraction is by means of the distraction and insertion tool as will be described below.
The cavity 412 in the proximal bone anchor 344 also includes a jam nut 440 with a distal end 442 and a proximal end 446. The jam nut 440 has set of external threads 444 adapted to engage with the set of internal threads. The jam nut 440 also has a driver engagement section 448 that is adapted to receive torque imparted by a corresponding driver such as a male hex driver. The torque input can cause the jam nut 440 to axially (distally) advance until it makes contact with the proximal pivot cup 420. The jam nut 440 shown in
The prosthetic nucleus 348 includes an outer membrane 460 and prosthetic nucleus material 464. As outer membrane 460 is filled with prosthetic nucleus material 464, the outer membrane 460 expands to conformably contact the inferior endplate of the distal vertebral body 304, the superior endplate of the proximal vertebral body 308, and the inner wall of the annulus fibrosus (not shown) which collectively define the boundaries of an intervertebral disc space 312.
Preferred prosthetic nucleus materials and systems comprise biomedical grade silicone elastomer e.g. silicone rubber, such as that obtained from Nusil Silicone Technology located in Carpeneria, Calif. or hydrogels or blends thereof (e.g., hydrogel/hydrogel, or hydrogel/elastomer). Cross-linked hyaluronic acid, such as is available from Fidia Corporation in Italy, is an example of a suitable material, however, many natural and man-made hydrogels or blends thereof may be configured to achieve similar properties without inflammatory response, such as those disclosed and described in and commonly assigned United States patent applications referenced above, and in detail in particular in U.S. Provisional Patent Application 60/599,989 filed Aug. 9, 2004, and 60/558,069 filed Mar. 31, 2004, each of which are incorporated in their entirety into this disclosure by reference
Distraction of the Motion Segment Though Use of Dissimilar Thread Pitches
Previously filed applications assigned to Trans1, Inc. have described a process for imposing a distraction on a motion segment (to move the two vertebral bodies away from each other along the z axis). For example see U.S. Pat. No. 6,921,403 for Method and Apparatus for Spinal Distraction and Fusion. Thus, when a threaded rod with a distal threaded section of a first, finer thread pitch engages with a distal vertebral body (after passing through a bore in the proximal vertebral body larger than the major diameter of the threads on the distal threaded section) and a proximal, coarser threaded section on the same threaded rod engages with a proximal vertebral body, the rotation of the two threaded sections with different thread pitches causes the distal finer pitched threads to advance into the distal vertebral body slower than the coarser threads advance into the proximal vertebral body. The net effect is that the engagement of the two threaded sections with the two vertebral bodies causes the two vertebral bodies to move apart.
Driving Two Threaded Implant Components
The implant components such as distal bone anchor 340 and proximal bone anchor 344 shown in
As part of preparing the axial channel 212, the distal vertebral body is bored through to create a bore hole approximately the size of the proximal bone anchor 344 less the external threads 404, or in other words approximately the size of the minor diameter of the external threads 404 of the proximal bone anchor 344. Likewise the axial channel 212 is extended at least partway into the distal vertebral body 304 and the bore size is approximately the size of the minor diameter of the external threads 356 on the distal bone anchor 340.
In the case of
A single driver engagement section 640 such as a female hex socket can be engaged with a corresponding driver to rotate, axially advance, and implant the dual anchor rod 620 into engagement with both the proximal vertebral body 604 and the distal vertebral body 608.
The decrease in major diameter between thread set 628 and thread set 648 has the disadvantage of decreasing the amount of interaction between the thread set 648 and the distal vertebral body 608. This decrease in major diameter is necessary when the pitches are not the same in order to avoid creating a helical thread path that the subsequent thread set 628 would be unable to follow due to the difference in thread pitch.
Thus, the example shown in
Some spinal implant assemblies, including spinal implant assemblies disclosed in and commonly assigned U.S. patent Ser. No. 11/256,810 filed Oct. 24, 2005 for Spinal Motion Preservation Assemblies (incorporated by reference herein) disclose assemblies where the component that is implanted in the distal vertebral body 608 is not rigidly connected to the component implanted in the proximal vertebral body 604. The two components may be connected at point of implantation into the vertebral bodies by a flexible membrane 460 (See
While the example given to illustrate the problem references a flexible membrane that is expanded to form the outer boundary of a prosthetic nucleus membrane, the problem would extend to other integral connections between the distal and proximal component that are insufficient to allow torque applied at driver engagement section 832 to drive the thread set 824 into the distal vertebral body 608.
For example, the previous applications and issued patents for assignee, TranS1 Inc. include teachings regarding the formation of a prosthetic nucleus using an injected barrier sealant material to seal the interior surfaces of the intervertebral disc space before injection prosthetic nucleus material. Components delivered as part of the process of a therapy using a barrier sealant material in lieu of a flexible membrane would, by definition, not be connected by a flexible membrane.
Thus, the prior art did not provide a suitable solution for use in the axial delivery of two components to two adjacent vertebral bodies nor did the prior art provide a suitable solution for the process of axial delivery of two components to two adjacent vertebral bodies combined with an imposed distraction of the vertebral bodies to be maintained by the insertion of prosthetic nucleus material.
One solution to the above-identified short comings in the prior art is shown in
One of skill in the art will recognize that while a hexagonal polygon is commonly used as a torque driver, other polygons could be used such as triangular, square, pentagonal, octagonal and so on. More complex shapes such as stars or non symmetric shapes could be used but a simple polygon is adequate.
Rotation of external sheath 2212 causes threaded engagement by external threads 2036 on proximal anchor retention coupler 2032 with corresponding threads on the proximal anchor. The sheath 2211 and attached proximal anchor retention coupler 2032 can rotate relative to the polygonal torque driver 2104. Retention pins 2220 retain the proximal anchor coupler 2032 to the sheath 2212.
A set of detailed drawings of the various components that comprise a dual anchor driver 2100 of the type shown in
As shown in
A dual hex head driver is a descriptive name for the driver shown in
The dual hex head driver and the polygonal torque driver described in connection with Example A can be manufactured in a variety of lengths so that the drivers can maintain the distal and proximal components at relative axial distances that are appropriate for both timed delivery of the proximal component (if timed delivery is used to avoid cross threading) and to adjust to the variations in anatomy between patients and the desired level of distraction.
A retention rod 2012 with external thread 2016 engages with the internal threaded section 368 of the distal bone anchor 1340. The retention rod 2012 can be rotated relative to the driver tip 2018 so that the distal bone anchor 1340 is pulled to contact the driver tip 2018.
Likewise a proximal anchor retention coupler 2088 with external threads 2092 can rotate relative to the driver tip 2018 as the proximal anchor retention coupler 2088 is attached to an external sheath 2096. Rotation of the proximal anchor retention coupler 2088 causes engagement between the external threads 2092 and the internal threads 416 of the proximal anchor 1344 to draw the proximal anchor 1344 down onto the shoulder 2008. With both anchors retained in contact with components of the keyed driver assembly 2000 the position of the distal bone anchor 1340 relative to the proximal bone anchor 1344 can be set based on the distances between the shoulder 2008 and the driver tip 2018. Control over the distances between the two separate bone anchors allows the two bone anchors with the same major diameter to be inserted without cross threading of the proximal vertebral body.
After the prosthetic nucleus material is allowed to cure, the insertion tool 2032 can be removed leaving behind a void in the prosthetic nucleus material where the insertion tool was during the formation of the prosthetic nucleus. (see element 348 on
The process 3200 for using a driver to first implant the distal and proximal devices, then insert one or more components before inserting a different tool to distract and then inject prosthetic nucleus material is summarized in
Step 3210 Load the device driver assembly with both the distal and proximal components. These two anchors, connected by a flexible membrane, are placed on the anchor driver assembly. The driver assembly uses an elongated torque driver, in this case a hexagonal shaped toque driver with an elongated section with a constant cross sectional (taken perpendicular to the longitudinal axis).
The step of loading the driver assembly includes seating the distal component onto the distal end of the driver wherein it is retained on the tip during insertion and axial, distal advancement by means of a threaded retention rod, and seating the proximal bone anchor on a shoulder within the dual anchor driver assembly through use of a proximal anchor retention coupler. Seating the two bone anchors on the driver assembly maintains a predetermined spatial separation between the distal component and proximal component and stretches the flexible membrane located there between so that the membrane slightly “necks in” and is less likely to be damaged while passing through the proximal vertebral body.
Step 3220 Insert the anchor driver assembly over a guide wire and advance the anchor driver assembly through the previously prepared axial channel that includes a bore through the proximal vertebral body and a bore in the distal vertebral body. The bore hole in the proximal vertebral body is about the size of the minor diameter of the external threads on both bone anchors.
Step 3230 Torque is applied using the anchor driver assembly to rotate and axially advance the distal bone anchor through the proximal vertebral body thereby creating a helical thread path through the first vertebral body.
Step 3240 Continued application of torque axially advances the bone anchors, which are held on the anchor driver assembly at a spatially maintained distance, to anchor the distal component into the distal vertebral body and anchor the proximal component into the proximal vertebral body without cross threading or rethreading in the proximal vertebral body.
Step 3250 Once the bone anchors are positioned into the respective vertebral bodies, release the distal bone anchor from the threaded engagement with the retention rod and release the proximal bone anchor from the proximal anchor retention coupler as the retention rod and the proximal anchor retention coupler can be rotated relative to the elongated hexagonal hex driver.
Step 3260 Remove the anchor driver assembly.
Step 3270 Insert the distal pivot cup by engaging the distal pivot cup with driver (not shown here) that employs a detent mechanism to engage the distal pivot cup. (Those with an interest in this particular driver can find it described in detail in co-pending application Ser. No. 11/256,810 which has been incorporated by reference.
Step 3280 Disengage the distal pivot cup driver from the distal pivot cup and remove the distal pivot cup driver.
Step 3290 Insert distractor/injector tool into the implanted bone anchors so that atraumatic tip of the distractor/injector tool contacts the distal pivot cup bearing surface. As it is undesirable to scratch or otherwise mar the bearing surface. The material selected for the atraumatic tip may be advantageously selected to be less hard than the bearing surface and smooth so it is not apt to scratch the bearing surface.
Step 3300 Move the distal vertebral body relative to the proximal vertebral body by axially advancing the distractor/injector tool relative to the proximal bone anchor through threaded engagement within the proximal bone anchor to push via an atraumatic tip on the distal pivot cup.
Step 3310 Inject prosthetic nucleus material through the interior of the distractor/injector and out apertures in fluid communication between the interior of the distractor/injector and the flexible membrane to expand and fill the flexible membrane sufficiently to form the prosthetic nucleus component of this prosthetic disc device, the prosthetic nucleus component being in conformal contact with the surfaces of the intervertebral disc space.
Step 3320 Allow the injected material to cure.
Step 3330 Remove the distractor/injector tool. This will leave a void in the cured injected material where the tool occupied volume in the intervertebral disc space during injection and curing. The cured prosthetic nucleus material should substantially retain the distraction imposed between the vertebral bodies. Subsequent processing steps during assembly of the spinal implant assembly could include a minor secondary distraction. Alternatively, the original distraction could be increased a small amount to compensate for any movement of cured injected material towards the void left by the removal of the distractor/injector.
There would be subsequent steps to complete the assembly of the particular spinal implant assembly and to close the surgical site but those steps are beyond the focus of the present invention.
Preferred materials for the various components shown in the drivers described above include components that are formed, i.e., machined, from among high strength (e.g., high tensile strength, high fatigue strength), wear and abrasion resistant metal alloys (e.g., MP35N; Elgiloy™, a super alloy of cobalt chrome; Co—Cr alloy such as Stellite™; Ti6Al4V alloy, and nitride coated Ti alloys) according to the biomechanical properties being selected by design (e.g., ability of driver to withstand torque while rotating to axially advance dual anchor implants through and into vertebral bone).
Whether done via a driver/injector or a distractor/injector tool, the membrane is expanded by means of high pressure injection, with a syringe, of prosthetic nucleus material (PNM) (e.g., saline, viscoelastic gel or an elastomeric solid or blends or combinations thereof), that is engaged by means of an integral Luer lock fitting that is configured to engage the handle at the proximal end of the MPA distractor/injector. A delivery tube or catheter, wherein the distal end of the tube is configured to engage the fitting in proximal end of the tool, and the proximal end of the tube engages a syringe attached thereon. The expandable membrane is enlarged or filled by means of apertures or fenestrations, e.g., through the slits or “cuts” in the cannulated rod comprising the in the torque driver (such as the dual hex head driver discussed above) or the distractor/injector tool, which enable fluid communication between the exterior and interior of the driver of the and through which prosthetic nucleus material is injected into the disc space, either directly, or via an intermediate (from about 6-12 mm of the overall deployed implant length) expandable membrane configured to be adhesively affixed and engaged by laser welding of a retainer ring, to or into the distal end of the proximal threaded anchor component and the proximal end of the distal threaded anchor component, respectively. In this manner, the expandable membrane inflates and extends into the intervertebral disc space previously distracted by means of the driver/injector or distractor/injector of the present invention, until when filled, it conformably contacts the surfaces within the intervertebral disc space. The ultimate expansion of the membrane is limited by contact with the end plates and the annulus, preventing rupture of the membrane due to over inflation. When filled and expanded in this manner with a suitable PNM, e.g., a hydrogel selected at least in part based on viscoelastic properties, the MPA is enabled to biomechanically perform the intended function of the motion restoration segment, e.g., the membrane, when filled with PNM, transfers hydrostatic pressure within the nuclear space into tensile “hoop stresses” in the annulus.
In one aspect of the invention, driver/injectors or distractor/injectors are configured to accommodate injection means with sufficient pressure/forces of substantially about 300 psi to deliver the PNM (or therapeutic, e.g., drug materials delivery) without accompanying shear forces that would fragment; denaturate; modify viscoelastic properties, e.g., rheology and/or compressibility; or otherwise render the therapeutic materials or PNM ineffective for their intended functionality (e.g., biomechanical motion segment mobility restoration/preservation in the case of PND with PNM). In a preferred embodiment, driver/injectors or distractor/injectors comprise at least one O-ring to enable injection of fluid(s) under pressure.
One of skill in the art will recognize that the alternative embodiments set forth above are not universally mutually exclusive and that in some cases alternative embodiments can be created that employ two or more of the variations described above. Likewise, the present invention is not limited to the specific examples or particular embodiments provided to promote understanding of the present invention. Moreover, the scope of the present invention covers the range of variations, modifications, and substitutes for the components described herein as would be known to those of skill in the art.
The legal limitations of the scope of the claimed invention are set forth in the claims that follow and extend to cover their legal equivalents. Those unfamiliar with the legal tests for equivalency should consult a person registered to practice before the United States Patent and Trademark Office.
|Brevet cité||Date de dépôt||Date de publication||Déposant||Titre|
|US640661||12 juin 1899||2 janv. 1900||Francis W Johnstone||Stay-bolt for steam-boilers.|
|US1007107||12 mars 1910||31 oct. 1911||Frederic Hulsmann||Screw-driving.|
|US1029104||24 juin 1911||11 juin 1912||Edward W Clark||Stay-bolt.|
|US1079224||21 sept. 1912||18 nov. 1913||Flannery Bolt Co||Stay-bolt.|
|US1086144||25 sept. 1911||3 févr. 1914||Flannery Bolt Co||Stay-bolt.|
|US1111691||5 mai 1913||22 sept. 1914||Flannery Bolt Co||Flexible stay-bolt for boilers.|
|US2243717 *||2 nov. 1938||27 mai 1941||Godoy Moreira Franciseo Elias||Surgical device|
|US2329398||23 janv. 1941||14 sept. 1943||Bernard A Duffy||Screw driver|
|US2550866 *||11 mai 1946||1 mai 1951||Rosan Joseph||Tool for installing inserts|
|US2586556||23 nov. 1946||19 févr. 1952||Mullikin Alfred||Flexible binder post|
|US3272541||8 févr. 1963||13 sept. 1966||Josef Latzen||Ball joints|
|US3367326||15 juin 1965||6 févr. 1968||Calvin H. Frazier||Intra spinal fixation rod|
|US3837347||20 avr. 1972||24 sept. 1974||Electro Catheter Corp||Inflatable balloon-type pacing probe|
|US4175555||22 févr. 1978||27 nov. 1979||Interfix Limited||Bone screw|
|US4276874||15 nov. 1978||7 juil. 1981||Datascope Corp.||Elongatable balloon catheter|
|US4297047||5 juin 1980||27 oct. 1981||Automotive Products Limited||Ball and socket joint|
|US4309777||13 nov. 1980||12 janv. 1982||Patil Arun A||Artificial intervertebral disc|
|US4636217||23 avr. 1985||13 janv. 1987||Regents Of The University Of Minnesota||Anterior spinal implant|
|US4854797||5 oct. 1988||8 août 1989||Ford Motor Company||Threaded fastener with resilient linking means|
|US4858601 *||27 mai 1988||22 août 1989||Glisson Richard R||Adjustable compression bone screw|
|US4875794||23 déc. 1987||24 oct. 1989||Dana Corporation||Preloaded steering ball joint assembly and method|
|US4878915||4 janv. 1989||7 nov. 1989||Brantigan John W||Surgical prosthetic implant facilitating vertebral interbody fusion|
|US4932925||21 juil. 1989||12 juin 1990||Ashworth Bros., Inc.||Link having a work-hardened area|
|US4932975||16 oct. 1989||12 juin 1990||Vanderbilt University||Vertebral prosthesis|
|US4959064||7 oct. 1988||25 sept. 1990||Boehringer Mannheim Corporation||Dynamic tension bone screw|
|US5002576||6 juin 1989||26 mars 1991||Mecron Medizinische Produkte Gmbh||Intervertebral disk endoprosthesis|
|US5059193||19 avr. 1990||22 oct. 1991||Spine-Tech, Inc.||Expandable spinal implant and surgical method|
|US5061137||29 avr. 1991||29 oct. 1991||Ford Motor Company||Fastener with resilient linking means|
|US5078718 *||17 avr. 1990||7 janv. 1992||Origin Medsystems, Inc.||Multi-part method and apparatus for removing pre-placed prosthetic joints and preparing for their replacement|
|US5102276||12 juil. 1990||7 avr. 1992||Ford Motor Company||Removable fastener with elastic linking means|
|US5108430||23 août 1990||28 avr. 1992||Biagio Ravo||Implantable reservoir adapted to receive and store structural devices therein|
|US5139499||5 sept. 1990||18 août 1992||American Cyanamid Company||Screw and driver|
|US5246458||7 oct. 1992||21 sept. 1993||Graham Donald V||Artificial disk|
|US5338297||19 mars 1993||16 août 1994||Kocur Medical Associates||Cervical canal balloon catheter|
|US5360430||29 juil. 1993||1 nov. 1994||Lin Chih I||Intervertebral locking device|
|US5433739||2 nov. 1993||18 juil. 1995||Sluijter; Menno E.||Method and apparatus for heating an intervertebral disc for relief of back pain|
|US5480401||10 févr. 1994||2 janv. 1996||Psi||Extra-discal inter-vertebral prosthesis for controlling the variations of the inter-vertebral distance by means of a double damper|
|US5489307||1 sept. 1994||6 févr. 1996||Spine-Tech, Inc.||Spinal stabilization surgical method|
|US5498265 *||1 avr. 1994||12 mars 1996||Howmedica Inc.||Screw and driver|
|US5562737||15 nov. 1994||8 oct. 1996||Henry Graf||Extra-discal intervertebral prosthesis|
|US5702453||13 mai 1996||30 déc. 1997||Sofamor Danek Group||Adjustable vertebral body replacement|
|US5733284||15 juil. 1994||31 mars 1998||Paulette Fairant||Device for anchoring spinal instrumentation on a vertebra|
|US5743912||14 août 1996||28 avr. 1998||Biomat||Upper femoral epiphysis osteosynthesis implant|
|US5827285||12 déc. 1996||27 oct. 1998||Bramlet; Dale G.||Multipiece interfragmentary fixation assembly|
|US6030162 *||18 déc. 1998||29 févr. 2000||Acumed, Inc.||Axial tension screw|
|US6056749||15 mars 1999||2 mai 2000||Spineology, Inc.||Method and device for fixing and correcting spondylolisthesis anteriorly|
|US6063121||29 juil. 1998||16 mai 2000||Xavier; Ravi||Vertebral body prosthesis|
|US6086589||2 févr. 1999||11 juil. 2000||Spineology, Inc.||Method and device for fixing spondylolisthesis posteriorly|
|US6093205||25 juin 1998||25 juil. 2000||Bridport-Gundry Plc C/O Pearsalls Implants||Surgical implant|
|US6125726 *||31 déc. 1997||3 oct. 2000||Emhart Inc.||Tool for attaching to an element for handling thereof|
|US6190413||16 avr. 1999||20 févr. 2001||Ulrich Gmbh & Co. Kg||Vertebral implant|
|US6235043||23 janv. 1997||22 mai 2001||Kyphon, Inc.||Inflatable device for use in surgical protocol relating to fixation of bone|
|US6258090||28 avr. 2000||10 juil. 2001||Roger P. Jackson||Closure for open ended medical implant and removal tool|
|US6319254||21 avr. 2000||20 nov. 2001||Newdeal||Compression osteosynthesis screw, and an ancillaty device for use therewith|
|US6428576||14 avr. 2000||6 août 2002||Endospine, Ltd.||System for repairing inter-vertebral discs|
|US6440168||2 sept. 1999||27 août 2002||Sdgi Holdings, Inc.||Articulating spinal implant|
|US6506194||8 juin 2000||14 janv. 2003||Mohammed Ali Hajianpour||Medullary plug including an external shield and an internal valve|
|US6517543||27 févr. 2001||11 févr. 2003||Pioneer Laboratories, Inc.||Bone connector system with anti-rotational feature|
|US6558386||10 oct. 2000||6 mai 2003||Trans1 Inc.||Axial spinal implant and method and apparatus for implanting an axial spinal implant within the vertebrae of the spine|
|US6558390||13 févr. 2001||6 mai 2003||Axiamed, Inc.||Methods and apparatus for performing therapeutic procedures in the spine|
|US6575979||16 août 2000||10 juin 2003||Axiamed, Inc.||Method and apparatus for providing posterior or anterior trans-sacral access to spinal vertebrae|
|US6582466||9 déc. 1999||24 juin 2003||Stryker Spine||Intervertebral disc prosthesis with reduced friction|
|US6582468||9 déc. 1999||24 juin 2003||Spryker Spine||Intervertebral disc prosthesis with compressible body|
|US6626943||23 août 2002||30 sept. 2003||Sulzer Orthopedics Ltd.||Artificial intervertebral disc|
|US6652535||5 oct. 2001||25 nov. 2003||Nobel Biocare Ab||Distraction osteogenesis fixture|
|US6656184||9 janv. 2002||2 déc. 2003||Biomet, Inc.||Bone screw with helical spring|
|US6669699||30 nov. 2001||30 déc. 2003||Spinecore, Inc.||Distraction instrument for use in anterior cervical fixation surgery|
|US6682561||25 mars 2002||27 janv. 2004||Pioneer Laboratories, Inc.||Spinal fixation system|
|US6692495||12 oct. 2000||17 févr. 2004||Fred Zacouto||Vertebral fixator and articulation|
|US6730088||16 mai 2002||4 mai 2004||Chung-Chun Yeh||Device for fixing spinal column under treatment|
|US6733532||9 déc. 1999||11 mai 2004||Stryker Spine||Intervertebral disc prosthesis with improved mechanical behavior|
|US6740090||10 nov. 2000||25 mai 2004||Trans1 Inc.||Methods and apparatus for forming shaped axial bores through spinal vertebrae|
|US6764489||27 mars 2002||20 juil. 2004||Novasive, Inc||Hinged anterior thoracic/lumbar plate|
|US6790210||10 nov. 2000||14 sept. 2004||Trans1, Inc.||Methods and apparatus for forming curved axial bores through spinal vertebrae|
|US6821277||21 déc. 2000||23 nov. 2004||University Of Southern California Patent And Copyright Administration||Percutaneous vertebral fusion system|
|US6899716||18 avr. 2002||31 mai 2005||Trans1, Inc.||Method and apparatus for spinal augmentation|
|US6899719||4 janv. 2001||31 mai 2005||Kyphon Inc.||Systems and methods for treating fractured or diseased bone using expandable bodies|
|US6921403||3 déc. 2002||26 juil. 2005||Trans1 Inc.||Method and apparatus for spinal distraction and fusion|
|US6964665||27 déc. 2001||15 nov. 2005||Thomas James C||Vertebral alignment system|
|US7014633||3 mai 2001||21 mars 2006||Trans1, Inc.||Methods of performing procedures in the spine|
|US7048717||27 sept. 2000||23 mai 2006||Essex Technology, Inc.||Rotate-to-advance catheterization system|
|US7077865||13 févr. 2003||18 juil. 2006||Disc Dynamics, Inc.||Method of making an intervertebral disc prosthesis|
|US7087058||10 juin 2003||8 août 2006||Trans1, Inc.||Method and apparatus for providing posterior or anterior trans-sacral access to spinal vertebrae|
|US7140281 *||24 janv. 2005||28 nov. 2006||Jim Ruff||Elastic connection wedge wrench|
|US7156877||24 mai 2002||2 janv. 2007||The Regents Of The University Of California||Biodegradable/bioactive nucleus pulposus implant and method for treating degenerated intervertebral discs|
|US7175626 *||15 juin 2004||13 févr. 2007||Board Of Regents Of The University Of Nebraska||Dynamic compression device and driving tool|
|US7291150||1 déc. 2000||6 nov. 2007||Sdgi Holdings, Inc.||Intervertebral stabilising device|
|US7361192||22 avr. 2005||22 avr. 2008||Doty Keith L||Spinal disc prosthesis and methods of use|
|US7419505||21 avr. 2005||2 sept. 2008||Fleischmann Lewis W||Collapsible, rotatable, and tiltable hydraulic spinal disc prosthesis system with selectable modular components|
|US7452359||7 juin 1995||18 nov. 2008||Warsaw Orthopedic, Inc.||Apparatus for inserting spinal implants|
|US7473256||22 oct. 2004||6 janv. 2009||Trans1 Inc.||Method and apparatus for spinal distraction|
|US7491236||22 oct. 2004||17 févr. 2009||Trans1, Inc.||Dual anchor prosthetic nucleus apparatus|
|US7547324||22 oct. 2004||16 juin 2009||Trans1, Inc.||Spinal mobility preservation apparatus having an expandable membrane|
|US20010021852||20 déc. 2000||13 sept. 2001||Chappius James L.||Fenestrated surgical screw and method|
|US20020035400||13 févr. 2001||21 mars 2002||Vincent Bryan||Implantable joint prosthesis|
|US20020068975||10 oct. 2001||6 juin 2002||Teitelbaum George P.||Formable orthopedic fixation system with cross linking|
|US20020198527||18 juin 2002||26 déc. 2002||Helmut Muckter||Implantable screw for stabilization of a joint or a bone fracture|
|US20030028193||2 juil. 2002||6 févr. 2003||Weil Lowell Scott||Self-tapping screw for small-bone surgery|
|US20030055427||1 déc. 2000||20 mars 2003||Henry Graf||Intervertebral stabilising device|
|US20030114930||18 déc. 2001||19 juin 2003||Lim Kit Yeng||Apparatus and method to stabilize and repair an intervertebral disc|
|US20030181982||4 mars 2003||25 sept. 2003||Spineology, Inc.||No-profile, lumbo-sacral fixation device and method|
|US20030204261||11 avr. 2003||30 oct. 2003||Lukas Eisermann||Articular disc prosthesis and method for implanting the same|
|US20040083002||22 oct. 2003||29 avr. 2004||Belef William Martin||Methods for treating spinal discs|
|US20040210227||30 janv. 2004||21 oct. 2004||Kinetikos Medical, Inc.||Compression screw apparatuses, systems and methods|
|US20040230309||13 févr. 2004||18 nov. 2004||Depuy Spine, Inc.||In-situ formed intervertebral fusion device and method|
|US20050043796||1 juil. 2004||24 févr. 2005||Grant Richard L.||Spinal disc nucleus implant|
|US20050113919||22 oct. 2004||26 mai 2005||Cragg Andrew H.||Prosthetic nucleus apparatus|
|US20050113929||22 oct. 2004||26 mai 2005||Cragg Andrew H.||Spinal mobility preservation apparatus|
|US20050149191||22 oct. 2004||7 juil. 2005||Cragg Andrew H.||Spinal mobility preservation apparatus having an expandable membrane|
|US20050154390||5 nov. 2004||14 juil. 2005||Lutz Biedermann||Stabilization device for bones comprising a spring element and manufacturing method for said spring element|
|US20050177167||7 avr. 2005||11 août 2005||Karl-Heinz Hildinger & Helmut Muckter||Implantable screw for stabilization of a joint or a bone fracture|
|US20050209602||9 nov. 2004||22 sept. 2005||Disc Dynamics, Inc.||Multi-stage biomaterial injection system for spinal implants|
|US20050277940 *||15 juin 2004||15 déc. 2005||Neff James R||Dynamic compression device and driving tool|
|US20060058800||13 août 2005||16 mars 2006||Trans1 Inc.||Methods and apparatus for provision of therapy to adjacent motion segments|
|US20060085073||18 oct. 2004||20 avr. 2006||Kamshad Raiszadeh||Medical device systems for the spine|
|US20060129147||8 avr. 2005||15 juin 2006||Biedermann Motech Gmbh||Elastic element for the use in a stabilization device for bones and vertebrae and method for the manufacture of such elastic element|
|US20060229609||18 mars 2005||12 oct. 2006||Chao-Jan Wang||Microadjustment spinal joint fixture|
|US20060264954||6 avr. 2006||23 nov. 2006||Sweeney Thomas M Ii||Active compression screw system and method for using the same|
|US20070106383||3 oct. 2006||10 mai 2007||Abdou M S||Devices and methods for inter-vertebral orthopedic device placement|
|US20070168042||20 mars 2006||19 juil. 2007||Hudgins Robert G||Devices and methods for disc replacement|
|WO1991000713A1||12 juin 1990||24 janv. 1991||Martin Nolde||Nucleus prosthesis with an introductory device and probe to determine the size of nucleus prosthesis required|
|Brevet citant||Date de dépôt||Date de publication||Déposant||Titre|
|US8343189 *||25 sept. 2008||1 janv. 2013||Zyga Technology, Inc.||Method and apparatus for facet joint stabilization|
|US8394125||24 juil. 2009||12 mars 2013||Zyga Technology, Inc.||Systems and methods for facet joint treatment|
|US8663293||11 avr. 2011||4 mars 2014||Zyga Technology, Inc.||Systems and methods for facet joint treatment|
|US8696707||7 mars 2006||15 avr. 2014||Zyga Technology, Inc.||Facet joint stabilization|
|US9017389||11 mars 2013||28 avr. 2015||Zyga Technology, Inc.||Methods for facet joint treatment|
|US9138219||15 juil. 2011||22 sept. 2015||Tarsus Medical Inc.||Methods and devices for treating a syndesmosis injury|
|US9186484||27 déc. 2013||17 nov. 2015||DePuy Synthes Products, Inc.||Guidewire insertion methods and devices|
|US9233006||15 nov. 2012||12 janv. 2016||Zyga Technology, Inc.||Systems and methods for facet joint treatment|
|US9289249||16 janv. 2014||22 mars 2016||DePuy Synthes Products, Inc.||Bone anchors and surgical instruments with integrated guide tips|
|US9314277||21 août 2013||19 avr. 2016||Zyga Technology, Inc.||Systems and methods for facet joint treatment|
|US9433445||14 mars 2013||6 sept. 2016||DePuy Synthes Products, Inc.||Bone anchors and surgical instruments with integrated guide tips|
|US9532884||26 mars 2014||3 janv. 2017||Nlt Spine Ltd.||Laterally deflectable implant|
|US20090138053 *||25 sept. 2008||28 mai 2009||Zyga Technology, Inc.||Method and apparatus for facet joint stabilization|
|US20140114365 *||30 déc. 2013||24 avr. 2014||Acumed Llc||Bone connector with pivotable joint|
|US20150327902 *||16 mai 2014||19 nov. 2015||Biomet C.V.||Method and apparatus for bone fixation|
|Classification aux États-Unis||606/99|
|Classification coopérative||A61B2017/00261, A61F2/441, A61F2002/4629, A61F2002/30507, A61B17/8888, A61F2002/30863, A61F2/4637, A61F2002/30566, A61B17/025, A61F2002/444, A61F2/4611, A61F2002/30563, A61F2002/4627, A61B2017/3445, A61F2/4425, A61F2002/443, A61F2002/30588, A61F2230/0069, A61F2250/0039, A61F2002/30235, A61F2/30742, A61F2002/30649, A61F2002/30405, A61F2002/30327, A61F2/4455, A61F2002/30581, A61F2210/0061, A61F2002/3085, A61F2220/0025, A61B17/3421, A61F2002/30495, A61B17/8897, A61F2002/30601, A61F2002/30075, A61F2002/3055, A61F2002/30665, A61F2002/30859, A61B2017/0256, A61B17/7055|
|Classification européenne||A61F2/46B7, A61F2/44D2, A61B17/02J, A61B17/70G, A61B17/88S4C|
|19 déc. 2005||AS||Assignment|
Owner name: TRANS1 INC., NORTH CAROLINA
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Year of fee payment: 4